CN1636150A - Ultrasound transducer - Google Patents

Ultrasound transducer Download PDF

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Publication number
CN1636150A
CN1636150A CNA028128826A CN02812882A CN1636150A CN 1636150 A CN1636150 A CN 1636150A CN A028128826 A CNA028128826 A CN A028128826A CN 02812882 A CN02812882 A CN 02812882A CN 1636150 A CN1636150 A CN 1636150A
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China
Prior art keywords
transducer
over cap
acoustic
bidimensional
imaging system
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Granted
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CNA028128826A
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CN100354651C (en
Inventor
W·J·奥斯曼
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Koninklijke Philips NV
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Koninklijke Philips Electronics NV
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4272—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue
    • A61B8/4281—Details of probe positioning or probe attachment to the patient involving the acoustic interface between the transducer and the tissue characterised by sound-transmitting media or devices for coupling the transducer to the tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4494—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer characterised by the arrangement of the transducer elements
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/892—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being curvilinear
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8925—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being a two-dimensional transducer configuration, i.e. matrix or orthogonal linear arrays
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52079—Constructional features
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/02—Mechanical acoustic impedances; Impedance matching, e.g. by horns; Acoustic resonators
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/18—Methods or devices for transmitting, conducting or directing sound
    • G10K11/26—Sound-focusing or directing, e.g. scanning
    • G10K11/34—Sound-focusing or directing, e.g. scanning using electrical steering of transducer arrays, e.g. beam steering
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0204—Acoustic sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/046—Arrangements of multiple sensors of the same type in a matrix array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/06—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/13—Tomography

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Radar, Positioning & Navigation (AREA)
  • Remote Sensing (AREA)
  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Biomedical Technology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Pathology (AREA)
  • Biophysics (AREA)
  • Multimedia (AREA)
  • Gynecology & Obstetrics (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)
  • Surgical Instruments (AREA)
  • Transducers For Ultrasonic Waves (AREA)
  • Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)

Abstract

An acoustic imaging system is described. A preferred system includes a protective cover configured to mate with a transducer body. The transducer includes a two-dimensional transducer element matrix array formed by a plurality of individually controllable transducer elements. The protective cover is superposed above the two-dimensional matrix array and is transparent to incident acoustic energy. Preferably, the protective cover is shaped to reduce patient discomfort and repetitive motion injuries to sonographers. Alternative embodiments comprise a shaped two-dimensional transducer element matrix array. Methods for improved ultrasound imaging are also provided.

Description

Ultrasonic transducer
The mutual reference of related application
It is that June 27 calendar year 2001, application serial no are the right of priority that name 60/301,282, that examination is unsettled is called the U.S. Patent application of " improved ultrasonic transducer " that the application requires the applying date, and its full content is hereby expressly incorporated by reference.
Technical field
The application generally relates to acoustics imaging.More specifically, the application relates to ultrasonic imaging system and the method for using the transducer with bidimensional transducer unit array.
Background technology
Ultrasonic imaging system becomes the important diagnostic instrument in many medical science subjects.A very big advantage of ultrasonic imaging system is a real time scan.For example, a ultrasonic imaging system can produce image so soon, so that the Ultrasound Instrument operator can in real time, alternatively scan the internal with reaching visual feedback or identify the interior motion of body, for example blood flow.This allows the Ultrasound Instrument operator to check the interested tissue of institute and revises in real time and check, improves quality of diagnosis thus and is examined number of patients.
Except that in real time, reach the advantage of visual feedback alternately, Ultrasound Instrument operator also is concerned about the resolution of system.In a ultrasonic imaging system, the resolution of system depends on the focusing power of system.The effective aperture of the transducer unit array in the probe that this focusing power depends on again with ultrasonic imaging system is connected.Current two types the transducer array column unit of layout use to(for) real-time ultrasound ripple imaging system.
A kind of layout comprises the annular array of single transducer unit or transducer unit.Use the ultrasonic imaging system of this transducer array arrangements of cells to depend on the mechanical motion of probe, so that beam of sound scans on interesting areas.
The layout of second kind of transducer array column unit comprises the transducer unit array by the electronic circuit excitation, and electronic circuit produces the time-delay that electronics is inducted in the sound wave output of transducer unit.These time-delays cause suitable phase retardation, and this phase retardation will make the beam of sound Be Controlled of transducer unit array generation and/or be focused.
Generation is used for being connected between electronic circuit and the transducer array column unit that receive to send pulse of transmission pulse of transducer array column unit being called as wave beam and forms passage.The Electronic Control of the beam of sound that the transducer unit array produces and/or focusing are based on a wave beam and form passage and connect a wave beam and form passage ground and send the pulse acquisition by electronic delay, to form an effective over cap with variable thickness.
Because some restrictions: (a) size and the complicacy of the cable of connection ultrasonic probe and disposal system, reach (b) number of obtainable wave beam formation passage in the ultrasonic system of reasonable price, electron focusing is limited in laterally on (direction that is parallel to imaging surface).Focusing on vertical direction (perpendicular to the direction of imaging surface) is that the mechanical lens of curvature realizes by placing fixedly on the probe face.
The improvement of traditional vertical focusing is to realize by the performance that changes probe aperture and/or mechanical lens.Can to change the depth of focus (high-frequency produces the focusing darker than low frequency) be known though change frequency, change frequency change the depth of focus be not considered to be favourable because the higher decay of low frequency in tissue relatively of frequency is faster.
Therefore, in order to change the vertical focusing of transducer unit array, be known that effective curvature of the lens that essential vertical aperture of change and/or change are relevant with the transducer unit array.For example, when the organ of a depths of imaging, lens must have the curvature of big aperture and appropriateness, and when shallow organ was changeed in one of imaging, lens must have less aperture and than small curve.
The crowd knows, transducer array column unit in ultrasonic probe can be arranged to one dimension (1-D) array, one and half dimension (1.5-D) array or bidimensional (2-D) arrays (typical sizes of 1-D transducer array column unit is that the magnitude and the in the vertical direction of 0.5 wavelength is the magnitude of 50 wavelength in the horizontal).In the 1-D array, transducer unit is usually placed in transversely, and in the vertical direction is individual unit row.Traditional phase linear array and curved arrays are regarded as 1-D transducer unit array usually.
In the 1.5D array, transducer unit be installed in laterally and vertical on, but control and data are electrically connected around vertical center and connect symmetrically, so that only can be controlled in the horizontal by the beam of sound that the 1.5D array produces.In the 2-D array, transducer unit be disposed in laterally and vertical on, and have to being arranged in transducer unit on this both direction and provide transmissions/reception to control and the electrical connection of pumping signal.Can on bidimensional, control and focus on by the beam of sound that the 2-D array produces.The example of 2-D array ultrasonic probe can be in U.S. Pat 5,186, sees in 175.
The advantage of 2-D array image-forming is well-known.For example, such advantage is included in (promptly on laterally reaching vertically) electronically controlled ability on two (2) dimensions, because vertically the improvement that focuses on has improved resolution, reaches the meticulous correction that relatively improves phase deviation by velocity of propagation.Dirigibility relevant with the 2-D transducer and improvement resolution have been cancelled the mechanically needs of the moulding acoustic lens of focused sound waves bundle.But transducer unit still needs protected.Therefore, the face of 2-D transducer is made of flat relatively acoustic window material layer.
Ultrasound Instrument operator can be by correctly being positioned at ultrasonic transducer the image that obtains a zone in the body on the health.In order to obtain to have the image of diagnostic value, Ultrasound Instrument operator must be by the position of sliding, rotate and/or tilting and popping one's head in and operate probe relative to patient.
Flat transducer face-as employed in the 2-D transducer-will make the image quality variation poor because the contact gear ratio of it and patient body tissue has a transducer of curved surface.Especially, flat transducer face causes parasitic reflection and stop portions sound wave aperture.Another shortcoming relevant with the transducer of plane surface configuration be, such transducer has sharpened edge, and it will make patient feel uncomfortable, or transducer has wide coverage rate to allow to form rounded edges.
Transducer with wide coverage rate configuration has also weakened contacting between transducer face and the patient body, and this will cause that the Ultrasound Instrument operator applies bigger pressure along the transducer longitudinal axis, to scheme to improve contacting between transducer face and the patient body.The increase of Ultrasound Instrument operator's applied pressure will produce patient's discomfort, reach repeatedly to move to injure the Ultrasound Instrument operator.Keeping suitably contacting problematic especially zone between transducer face and patient body is intercostal heart and breast imaging.Usually, use for this class, the 2-D transducer unit array that transducer housing comprises is selected expectedly to strengthen resolution with improving vertically to focus on.
Therefore, need a kind of transducer of improvement, it can overcome these and/or other the shortcoming relevant with traditional transducers.
Summary of the invention
The embodiment of the ultrasonic transducer that improves can be used as the system that acoustics imaging is provided.In a preferred embodiment, this system comprises that is designed for a moulding over cap that mates with the transducer main body.Over cap is made of the material with such acoustic characteristic at least in part: it makes by this material to treating that the ultrasonic energy in the imaging object changes direction.This moulding over cap makes patient feel comfortably cool, increase the sound window and reduces to repeat to move the incidence that injures the Ultrasound Instrument operator.The ultrasonic imaging system that is made of the transducer that improves carries out electron focusing to the acoustic energy that passes over cap.
The method that provides for example patient's acoustics imaging is provided other embodiments of the invention.A preferable methods may further comprise the steps: (1) is provided with a transducer, and this transducer has the moulding over cap that is made by acoustics focusing material at least in part; (2) from the over cap conduct acoustic waves; (3) receive from treating the sound wave of imaging in-vivo tissue reflected back; (4) convert described reception sound wave to electric signal; And (5) handle described electric signal to produce image.
Those of ordinary skill in the art will be appreciated that other system, method and the feature of the ultrasonic transducer of improvement based on the investigation to the following drawings and detailed description.Therefore try hard to make all these spare systems, method and feature to be included in this explanation, in the scope of the ultrasonic transducer of this improvement and the protection of claims of being set up.
Description of drawings
Can understand this improved ultrasonic transducer better with reference to the following drawings.Parts in the accompanying drawing are unnecessary to be provided in proportion; And what need emphasize is that it can provide clearly the principle of transducer and describes.In addition, similar label is represented corresponding part in a plurality of accompanying drawings.
Fig. 1 is the general diagrammatic sketch that expression sends to acoustic energy the tradition 1 dimension transducer in the corresponding object.
Fig. 2 is the general diagrammatic sketch of improved ultrasonic transducer of expression and image processing system.
Fig. 3 is the general diagrammatic sketch of the improved ultrasonic transducer among Fig. 2 of presentation image disposal system details.
Fig. 4 is the general diagrammatic sketch of the transducer unit control of improved ultrasonic transducer in the presentation graphs 2.
Fig. 5 A is the part cross-sectional side view of an embodiment of improved ultrasonic transducer in the presentation graphs 2.
Fig. 5 B is the side view of another embodiment of improved ultrasonic transducer in the presentation graphs 2.
Fig. 6 is a process flow diagram of describing the preferred function of imaging system among Fig. 2.
Fig. 7 A is the planimetric map of another embodiment of the present invention.
Fig. 7 B is the general diagrammatic sketch of the details of over cap among the presentation graphs 7A.
Fig. 8 A is the planimetric map of another embodiment of improved ultrasonic transducer.
Fig. 8 B is the general diagrammatic sketch of the details of over cap among presentation graphs 8 A.
Fig. 9 represents the general diagrammatic sketch that improved ultrasonic transducer demonstration is placed during the representational breast imaging process.
Figure 10 represents to be used for that being operated in of an object of imaging sends and the general diagrammatic sketch of an acoustic beam of receive mode.
Figure 11 represents to be used for that being operated in of a plurality of objects of imaging sends and the general diagrammatic sketch of a plurality of acoustic beams of receive mode.
The general diagrammatic sketch of the spatial relationship between the over cap of the improved transducer of Figure 12 presentation graphs 2 and the bidimensional transducer unit array.
Embodiment
Tradition 1 dimension (1-D) phased array transducers that is used for ultrasonic imaging generally includes the lens of the beam of sound focusing that will be sent by transducer.Especially, the machine configurations of this lens normally is selected to the beam of sound from transducer is focused in a vertical dimension.Also can be by making concave and mechanically focus on this vertical dimension (direction) such as listing at transducer array.Laterally dimension (direction) is typically by electron focusing.
As an example, tradition 1 dimension (1-D) phased array transducers uses a kind of lens, and these lens can impel the acoustic energy that sends to focus in an object, for example human body.Usually, the acoustic velocity that has of this lens material is less than the acoustic velocity (approximate 1.5mm/ μ sec (microsecond)) of human body.Therefore supposition is tending towards covering or focusing in the object by the acoustic energy that the sound wave lens propagate in the object by ultrasonic transducer.Summarily expressing the acoustic energy that is sent by traditional 1-D transducer among Fig. 1 focuses in the object.
The sound wave 12,14,16,18 and 20 of expressing demonstration in Fig. 1 sends from transducer 22 by a condenser lens 24.As shown in this Fig, owing to the material of lens 24, the sound wave trend focuses on when sound wave is propagated in object 30 more deeply at least in part.
As everyone knows, depend on acoustic velocity and the acoustic impedance by the material wherein propagated of acoustic energy for example, acoustic energy is propagated with various speed and with various wavefront shape.For example, the velocity of sound of lens material is more near the velocity of sound of object, and is more approaching on incident angle with the energy that enters in the object by the energy that transducer sends.In addition, the acoustic impedance of lens material is more near the acoustic impedance of object, and more ultrasonic energy can send to the object from transducer.
As shown in Figure 2, this imaging system preferred embodiment 200 comprises a transducer probe (" transducer ") 202.As an example, transducer 202 can be bidimensional (2-D) phased array transducers.Transducer 202 is electrically connected to an image processing system 204.204 pairs of transducers 202 of image processing system provide various signals, so that transducer 202 can send acoustic energy by a plurality of transducer units that are arranged in energy converter planar 207 peripheries with the 2-D array way.Acoustic energy that sends and the echo that is reflected can pass the over cap of being made by the material that can see through sound wave 206.Transducer 202 converts the sound echo of reflected back electric signal to and turns back to image processing system.
Over cap 206 relative transducer main bodys 208 are held in place by the fore-end 210 of transducer main body 208.Especially, over cap 206 is suitable for being seated at least in part in the hole (not shown) that is limited by fore-end 210.But other various configurations also can be used.
In the transducer of prior art, over cap 206 is designed to the lens of a non-focusing sound wave.More specifically, over cap 206 is made of the material of selecting and/or is special shape, and it allows acoustic energy propagates to object, in human body, and can mechanically not focus on acoustic energy basically.As an example, can comprise an over cap 206 among the prior art embodiment of ultrasonic transducer 200, it is made of acoustic matching material at least in part.This acoustic matching material preferably has the velocity of sound of adaptive typical object and the velocity of sound and the acoustic impedance of acoustic impedance basically.
In other prior art embodiment, non-focusing is to keep uniform thickness to realize by transducer face 207 being made part over cap 206 flat or convex curvature and in the path that is arranged in sound wave.For example, a kind of have the velocity of sound and can be considered as the acoustic matching material that is used for medical diagnostic applications at the material of about 1.4mm/ μ sec to about 1.6mm/ μ sec scope.Acoustic matching material preferably also has the acoustic impedance to about 1.7Mrayl scope at about 1.3Mrayl (million Rayleighs).
In certain embodiments, the over cap 206 of non-focusing sound wave can be made of butadiene, styrene butadiene and/or relevant all kinds of rubber and/or polymkeric substance.These materials typically are being about 8dB/cm for about 3dB/cm reaches on the 2MHz to the decay of acoustic energy on 5MHz.The crowd knows that traditional lens material such as silicon on 5MHz are being about 33dB/cm for about 9dB/cm reaches to the decay of acoustic energy on the 2MHz.
Be noted that those skilled in the art can select to be provided with an over cap 2 06, it is made up of the material that individually is not considered acoustic matching material.But, these combinations of materials can present the acoustic matching characteristic together, for example the velocity of sound about 1.4mm/ μ sec to about 1.6mm/ μ sec scope and acoustic impedance at about 1.3Mrayl extremely in about 1.7Mrayl scope, the combination of these materials then can consider to be used for improved ultrasonic transducer.
By the over cap 206 that the non-focusing sound wave is set, imaging system 200 can be suitable for laterally and the vertical dimension acoustic energy that son focuses on that powers on send among the patient body.In fact, imaging system 200 can provide the beam of sound that helps sensitive relatively electrofocusing.Compare with other ultrasonic imaging system that uses the mechanical focus lens, this will help to improve the varifocal imaging function.Also can infer, use the imaging system of the over cap 206 of non-focusing sound wave that the beam of sound that is particularly suitable for contrasting imaging applications can be provided.Following will the detailed description in detail, improved imaging system can comprise the over cap 206 of different shape, it is made of acoustic matching material at least in part.
A shortcoming of prior art is that the use of the over cap 206 of non-focusing sound wave may be undesirable.Other requires suitable acoustic matching material as permanance, chemical resistance and bio-compatibility can't obtain maybe the needs exploitation that keeps punching to satisfy transducer.In addition, need to keep the shape that may stipulate the over cap surface that contacts between transducer 202 and the patient, this shape will make acoustic energy focus in fact.Improved ultrasonic transducer 202 improves ultrasound imaging techniques by the electronic compensation of over cap 206 focus characteristics.
Referring now to Fig. 3 in detail, the preferred embodiment of image processing system 204 will be described.Be appreciated that Fig. 3 need not to represent each ingredient of this optimum decision system, but focus on system disclosed herein and/or the maximally related ingredient of method on.
As shown in Figure 3, image processing system 204 comprises improved transducer 202, and it is electrically connected with the T/R switch 302 of image processing system 204.T/R switch 302 places transducer 202 and sends or receive mode.For the ease of sending acoustic energy in send mode operating period by transducer 202, image processing system 204 comprises and sends Beam-former 304 that it is provided with the transmission frequency f0 and the amplitude of various transmission signals.Send Beam-former 304 and be connected with transmission waveform modulated device 306, the latter produces each and sends signal wire.As shown in Figure 3, transmission Beam-former 304 and transmission waveform modulated device 306 are operated under the control of central controller 310.
In order to help receiving acoustic energy by transducer 202 in receive mode operating period, image processing system 204 comprises an A/D converter 312, and it will change into digital signal by the simulating signal that transducer 202 receives.Digital filter 314 is the required receiving belt signal in addition of RF wave filter elimination from receive data for example.Then received beam forms device 316 and receives the filtered digital signal that representative receives ultrasonic echo.
Received beam forms device 316 and can be designed to receive a plurality of digital echo signal waveforms (corresponding to many groups transducer unit of the 2-D array of transducer unit) from A/D converter 314.Received beam forms device 316 a plurality of digitizing echo waveforms capable of being combined to form single sound wave line.In order to finish this task, the treatment channel a plurality of arranged side by side in received beam formation device 316 will make each echo waveform postpone the times of different amounts and these time-delay waveforms will be stacked up, to produce a compound digital sound swash.In addition, received beam forms that device 316 can receive a series of data sets of each sound wave line in time in succession and with the pipeline processing mode deal with data.
Presentation manager 318 can comprise the random-access memory (ram) of suitable type and can be designed for from a series of digital composite sound wave line of received beam formation device 316 receptions.The sound wave line can be limited in the three-dimensional coordinate space.Presentation manager 318 can be designed the picture information in processing reception of mathematics ground and the filtering figure sound wave line.In addition, presentation manager 318 can be designed the sound wave line of collecting data on signal processing time.In this respect, presentation manager 318 also can comprise a scan converter, is stored in data among the RAM with conversion, so that produce the pixel that is used to show.In case whole Frame (i.e. one group of all sound wave line in single image or image/picture to be shown) is collected by RAM, each scan converter will be handled the data among the RAM.
For example, if use relative position ground that polar coordinates limit echo information with data storage in RAM, scan converter converts polar data to vertically (quadrature) data, but so that can carry out raster scanning by the processor of raster.Ultrasonic imaging system 204 is finished reception, echo recovers and image processing function, after forming a plurality of picture frames relevant with a plurality of ultrasonogram image planes the echo-image data message is sent to video processor shown in Figure 3 320.
Video processor 320 can be designed to receive the echo-image data message and can be designed to the picture information raster scanning.Video processor 320 produces image cell (being pixel), and it will be sent to display device 322.In addition, image cell can be sent to the video memory device (not shown).Video memory device can comprise digital video disc (DVD) player/recorder, compact disc (CD) player/recorder, video cassette recorder (VCR) or out of Memory memory storage.As commonly known in the art, these video storage devices allow user/operator to watch image or follow-up data to collect image processing in non real-time.
Also as shown in Figure 3, display device 322 can be designed to receive image cell (being pixel data) and drive suitable display screen or other imaging device (as printer/plotting apparatus) from video processor 320, so that observe ultrasonic image.
Many modification of the image processing system 204 shown in Fig. 3 can be worked with improved ultrasonic transducer 202.For example, but received beam forms device 316 separated into two parts, and a simulation part (not shown) is set at and reaches the back that a numerical portion is set at digital filter 314 between T/R switch 302 shown in Figure 3 and the A/D converter 312.
Referring now to Fig. 4, the general diagrammatic sketch of its expression transducer control system 400.These transducer control system 400 control bidimensional transducer unit arrays 402.Bidimensional transducer unit array 402 comprises a plurality of ultrasonic transducers unit, and for example some are represented with label 408,412 and 414 in them.These ultrasonic transducer unit 408,412 and 414 are arranged embarks on journey and is listed as, and some in them are for example represented with label 404 and 406 respectively.This configuration is called as matrix array sometimes.But the layout of other transducer unit also is possible.
Though on Fig. 4, summarily represented one 8 * 14 planar ultrasonic wave transducer unit array, but should point out, design of the present invention can be used for any bidimensional ultrasonic transducer cell array configuration, comprises the configuration that ultrasonic transducer unit wherein is bent on or two of two dimensions.For example, that bidimensional ultrasonic transducer cell array can have is cylindrical, sphere shape, annular surface shape or other curve form, and also can use and the wave beam relevant with the plane bidimensional ultrasonic transducer cell array 402 shown in Fig. 4 formed the wave beam that changes a little form.
Each unit 408,412 and 414 of bidimensional transducer unit array 400 can individually be controlled.Especially, each transducer unit 408,412 and 414 can be used as transmitting element and as receiving element work, reaches each unit and receive the signal of being controlled individually.For example, ultrasonic transducer unit 408 is electrically connected to transmission/reception (T/R) switch 418 by connecting line 416.This T/R switch 418 is by the signal (not shown) control from central controller 310, to allow transducer unit 408 with send mode and receive mode work.
When transducer unit 408 was used for send mode, transducer unit 408 received from the transmission pulse that sends Beam-former 304 by connecting line 426, adjustable amplifier 422 and connecting line 424.Adjustable amplifier 422 is used to limit the characteristic of the transmission pulse that imposes on transducer unit 408 and is controlled by amplitude controller 420 by connecting line 430.Though done omission for simplicity's sake, each unit in bidimensional transducer unit array 402 comprises a similar controlled adjustable amplifier.
When transducer unit 408 is used for receive mode, incides transducer unit 408 lip-deep ultrasonic energies and be converted to electric signal.This electric signal is by connecting line 416, T/R switch 418 (it is now by being operationally connected to connecting line 444 from the control signal of central controller 310), and received signal is supplied to variable gain amplifier 446 thus.Variable gain amplifier 446 amplifies the electric signal that receives and this signal is offered delay unit 484 by connecting line 448.
Similarly, transducer unit 412 receives by connecting line 436 and sends pulse and by connecting line 438 received signal is supplied with variable gain amplifier 442.Variable gain amplifier 442 offers delay unit 482 with the electric signal that receives by connecting line 458.Similarly, transducer unit 414 receives by connecting line 458, switch 456 and connecting line 454 and sends signal, and by connecting line 454, switch 456 and connecting line 462 received signal is supplied with variable gain amplifier 464.Variable gain amplifier 464 offers delay unit 478 by connecting line 466 with the received signal of amplifying.Each unit in the bidimensional transducer unit array 402 is controlled in this wise, allows thus each unit in the bidimensional transducer unit array 402 is controlled all sidedly.
Variable gain amplifier 462,442 and 446 and delay unit 478,482 and 484 all be included in received beam and form in the device 316.Though shown in the figure only is three variable gain amplifiers and three delay units, received beam forms amplifier and the delay circuit (and other treatment circuit) that device 316 comprises abundant each transducer unit that is used for bidimensional transducer unit array 402.In addition, can form that device 316 is carried out various multipath conversion, beamlet forms and other signal processing technology by received beam.But for simplicity of illustration, the received beam among Fig. 2 forms device 316 and only comprises three delay units.Each amplifier that received beam forms in the device 316 passes through connecting line 480 by the signal controlling from central controller 310.The definite receiving gain that provides by each variable gain amplifier 464,442 and 446 of signal on the connecting line 480.The gain that is provided by each amplifier is variable.Similarly, each delay unit 478,482 and 484 is by passing through the signal operation of connecting line 474 from central controller 310.This control signal determines that each delay unit 478,482 and 484 imposes on the amount of delay of corresponding received signal.Similarly, in this way, available pinpoint accuracy control receiving aperture is because comprise separately variable gain amplifier 442,446 and 564 and control circuit at each transducer unit of bidimensional transducer unit array 402.
Delay unit 478,482 and 484 output respectively offer sum unit 494 by connecting line 486,488 and 492.Sum unit 494 makes up the output of each delay unit and wave beam is formed signal and offers other processing unit by connecting line 496, as presentation manager 318 (not shown).In another configuration, variable gain amplifier 464,442 and 446 can lay respectively at the back of delay unit 478,482 and 484.In addition, delay unit 478,482 and 484 output one-tenth subarray capable of being combined, and can before or after delay unit separately, apply adjustable gain in sub-array signal in sum unit 494 fronts to each subarray.
Importantly, the bidimensional transducer unit array 402 with each controlled transducer unit 408,412 and 414 makes the ultrasonic pulse patterns that send out to change in bidimensional.Especially, bidimensional transducer unit array 402 can be in array with respect to the position Be Controlled of each unit.By the control fully on whole aperture, bidimensional transducer unit array control system 400 allows the wave beam zone in aperture with the pinpoint accuracy Be Controlled.
The time-delay of using in sending Beam-former 304 and received beam formation device 316 is calculated and can be understood with reference to Figure 10, wishes focused image on target 1002 in the figure, and this target is for example by certain structure organization in the imaging object 30.In the case, the acoustic energy that sends from bidimensional transducer unit array 402 is focused on target 1002 and received beam and forms device 316 acoustic energy that receives is focused on to increase the receiving sensitivity on the target 1002 to greatest extent.In order to be sent in the acoustic energy that focuses on the target 1002, central controller 310 can be by 468 pairs of bidimensional transducer units of connecting line array 402 the transmission Beam-former 304 of each unit delay control signal is provided and synchronizing signal is provided, with the time reference that is used to delay time.Behind synchronizing pulse, send Beam-former 304 and cause that sending signal forms time-delay T with wave beam BFOffer each unit of bidimensional transducer unit array 402 by for example connecting line 426, variable gain amplifier 422, connecting line 424, T/R switch 418 and connecting line 416.Send wave beam and form time-delay T BFUsually each unit for bidimensional transducer unit array 402 is different and can calculates as described below.Send acoustic energy in time T pIn propagate into target, this time is provided by following formula:
T p = 1 v b - ( x - x 0 ) 2 + ( y - y 0 ) 2 + ( z - z 0 ) 2 , Formula 1
V in the formula bBe the acoustic wave propagation velocity in the object, the two-dimensional array unit is at coordinate (x 0, y 0, z 0) on, and target 1002 coordinate (x, y, z) on.Arrive can calculating as follows T.T. of target 1002 from synchronizing pulse to the acoustic energy that sends:
T=T BF+ T pFormula 2
For acoustic energy being focused on the target 1002, send wave beam and form time-delay T BFMust be selected like this,, make acoustic energy arrive target 1002 simultaneously thus from all two-dimensional array unit so that the T that always delays time is identical for each unit.Any one group of transmission wave beam of the condition that the satisfied T.T. T from synchronizing pulse to the acoustic energy arrival target 1002 that is sent by each unit of energy is identical forms the T that delays time BFBe sufficient.Can be known by above-mentioned discussion and to find out, be the focusing that obtains on target 1002, sends wave beam and form time-delay T BFDifference stipulate by geometric arrangement fully.
In receiving cycle, each unit of bidimensional transducer unit array 402 is at propagation delay T pThe back receives the acoustic energy by target 1002 reflections, this T that delays time pThe propagation delay of unit is identical during with transmission.For target is positioned on the focus, received beam forms device 316 makes the receiving signal delayed received beam from each unit form time-delay T BF, it is identical with transmission wave beam formation time-delay.Form identically with sending wave beam, any one group of wave beam forms time-delay and can be used, and is suitable as long as the wave beam between any two unit forms delay inequality.
In addition, along with the increase of the time behind the synchronizing pulse, because of the limited velocity of propagation of acoustic energy, the acoustic signals that arrives bidimensional transducer unit array 402 is caused by the reflection on the target on the deep gradually degree of depth.Received beam forms time-delay T BFThe function that can be used as the degree of depth changes provides collectiong focusing to be provided on all types of target degree of depth.This is called as dynamic collectiong focusing.
At bidimensional transducer unit array 402 and treat that inserting an over cap 206 between the object 30 of imaging can change propagation delay a value, this value and over cap 206 and treat in the object 30 of imaging the velocity of sound, and the thickness of over cap 206 relevant.Especially, over cap 206 has added the time-delay T of over cap c, this time-delay provides by following formula is approximate:
T c = h × ( 1 v c - 1 v b ) , Formula 3
H represents the thickness and the v of over cap 206 in the formula cBe the velocity of sound in the over cap 206.If over cap 206 is made by acoustic matching material, then v cBe approximately equal to v bAnd the time-delay T of over cap cBe approximately equal to zero, and do not need to change wave beam formation time-delay T BFIn addition, if the thickness h of over cap 206 is identical for all unit, over cap time-delay T then cFor all transducer units is identical, and no matter speed v cHow.Because the difference that only has wave beam to form time-delay is important, can find out easily that the over cap 206 of uniform thickness does not change required wave beam and forms time-delay T BF
If but on bidimensional transducer unit array 402 inhomogeneous the and speed v of thickness h cBe different from speed v b, then for each unit time-delay T shown in Figure 12 cTo be different.This will cause in the transmission cycle wavefront distortion that enters over cap 206 wavefront distortion penetrated from over cap 206 and the receiving cycle, and consequently loss of Ju Jiaoing and image blurs.Send Beam-former 304 and received beam and form the nominal value that the time-delay used in the device 316 can obtain by distance calculation relatively and change, eliminate the time-delay that the non-uniform thickness by over cap 206 causes thus and change, so just maintenance focusing and image quality.In other words, the time-delay of new Beam-former equal primary beam form the device time-delay deduct the over cap time-delay or:
T New=T BF-T cFormula 4
Final any new Beam-former time-delay for negative situation under, can add constant time-delay to all Beam-former passages, so that all time-delays are for just.For example, bidimensional transducer unit array 402 is covered by an over cap 206 in Figure 12, and this over cap has non-uniform thickness, and the thickness on a representative unit 1204 is h thus 1204, and the thickness on another representative unit 1206 is h 1206Total propagation delay of 1202 is from representative unit 1204 to reference surface:
T 1204 = h ref v b + h 1204 × ( 1 v c - 1 v b ) Formula 5
And from representative unit 1206 to reference surface total propagation delay of 1202 is:
T 1206 = h ref v b + h 1206 × ( 1 v c - 1 v b ) Formula 6
Under the most common operating conditions that runs into, the above-mentioned program that is used for the time-delay of compute beam formation device can be enough to produce good focusing.But, in this program, comprising approximately, promptly the variation in aperture is all identical to all steering angles and the depth of focus in the time-delay that is produced by over cap 206.
If relatively greater than having the about three times zone of a radius-of-curvature less than its overlay area width to the thickness of the distance of required focus point or over cap 206 greater than the about three times of wavelength or the over cap 206 of incident ultrasonic energy, this is similar to can not be enough accurate greater than the effective aperture of 45 degree or transducer 202 at the beam steering angle of transducer face.
Figure 11 represents an example of this effect.Here, acoustic energy 1102 propagates into target 1120 along ray 1103 from the unit, and 1112 propagates into target 1120 along ray 1113 and refracted ray 1114 from the unit.Acoustic energy also 1102 propagates into target 1140 along ray 1104 and refracted ray 1105 from the unit, and 1112 propagates into target 1140 along ray 1115 and refracted ray 1116 from the unit.Though diagram not in scale, find out that obviously by over cap 206 and through treating that the diffusion path length of imaging object 30 is different for two different targets, reaching these differences also is distinguishing for two transducer units 1102 and 1112.Therefore, the time-delay Tc by over cap 206 is not only cell position and is the function of target location.Those of ordinary skill in the art will understand, and the figure shown in Figure 11 only provides concise and to the point explanation.The individual transducers unit can not oneself be focused on by them.Next works the beam of sound that passes the aperture is focused on a plurality of effective transducer units in image processing system 204 control.
Now again notice is got back to the bidimensional matrix of controlled transducer unit shown in Figure 4.Layout permission among Fig. 4 will be sampled entirely, the bidimensional time-delay of controlled, any (referring to unrestricted) distributes imposes on bidimensional transducer unit array 402.The term of full sampling is meant that each transducer unit 402,412 and 414 is individually controlled.In a preferred embodiment of this layout, each of bidimensional transducer unit array 402 other transducer unit receives the control signal from some mode of central controller 310.
The time-delay of bidimensional transducer unit array aperture distribute be one of the aperture arbitrarily, the bidimensional function in full sampling, controlled aperture.Therefore this time-delay distributes and can be adjusted to compensate the over cap 206 of Any shape; with the shape that allows over cap 206 be determined to be can provide with the best for the treatment of imaging object 30 contact, desirable ergonomics quality or above-mentioned other characteristic; as previously mentioned, and can not reduce image quality.
With reference now to Fig. 5 A and 5B, come some preferred embodiment of more detailed description transducer 202.As shown in Fig. 5 A, transducer 202 comprises the bidimensional transducer unit array 502 of a main body 208 and a moulding.As shown in the figure, this bidimensional transducer unit array 502 can comprise a plurality of transducer units 408,412 (only illustrating two for ease of diagram).Main body 208 preferably is designed to hold one or more required parts, so that send and/or receive acoustic energy by bidimensional transducer unit array 502.Should point out that in the figure, fore-end 210 and over cap 206 are removed to expose bidimensional transducer unit array 502.Shown in the part cross-sectional side view of Fig. 5 A, this bidimensional transducer unit array 502 is a cylindrical shape.Should be appreciated that sphere shape bidimensional transducer unit array 502 can selectedly as requested be used in transducer 202 and need keep the tight occasion that contacts with each surface of human body.
In addition, main body 208 can be the design of ergonomics, so that correct position transducer 202 is carried out imaging process.Main body 208 comprises a center section 504, and it is suitable for the person's of being operated hand and catches.In addition, main body 208 can be covered by a kind of material, and it not only protects the electronic section of transducer, and has and make transducer 202 be easy to the function of being caught by the Ultrasound Instrument operator.
In Fig. 5 A illustrated embodiment, main body 208 comprises an over cap mounting portion 506, and it preferably magnifies radially outwardly being fit to from middle part 504 and cooperates with over cap 206 (not shown).Transducer 202 near the end, be to be provided with a tapering part or neck 512 on the end back face portion 506.Neck 512 defines the aperture that is used to accept cable 520.Cable 520 is used for being electrically connected easily between transducer 202 and image processing system 204 (not shown).
Can use the over cap 206 of different shape to protect and shield following moulding bidimensional transducer unit array 502.Preferably its shape closely cooperates with following bidimensional transducer unit array 502, is coupled so that suitable sound wave to be provided.For various considerations, for example between over cap 206 and patient, form excellent contact, for image quality and patient comfort and be easy to use Ultrasound Instrument, can make special shape so that be more suitable for special ultrasonic inspection.For example, in certain embodiments, but over cap 206 actual design become transducer 202 is aimed at patient's sound wave receiver window.Especially, this over cap 206 preferably includes from transducer 202 outward extending curved surfaces.This configuration trend makes the convenient location of over cap 206 relative sound wave receiver windows, and this sound wave receiver window is for example determined by the adjacent rib of patient.More specifically, normally cooperate and tend to make between curved surface and rib and organize the composition surface to aim at the sound wave window.As described below, organize the composition surface can be provided with various configurations.
Shown in Fig. 5 B, transducer 202 comprises a main body 208 and a moulding bidimensional transducer unit array 552.As shown in the drawing, bidimensional transducer unit array 552 can comprise a plurality of transducer units 408,412 (only illustrating two for ease of diagram).Here also as above figure is such, and fore-end 210 and over cap 206 are removed to expose bidimensional transducer unit array 552.Shown in the side view of Fig. 5 B, this bidimensional transducer unit array 552 is essentially spherical shape.Spherical bidimensional transducer unit array 552 can selectedly as requested be used in transducer 202 need keep the tight occasion that contacts with each surface of human body.Should be appreciated that the bidimensional transducer unit array 402 with annular surface or other curved surface (as anticlastic surface) is possible, and can use the wave beam in the plane bidimensional transducer unit array 402 shown in Figure 4 relatively to form the wave beam formation of revising a little.
Referring now to Fig. 6, an improved method for ultrasonic imaging of bidimensional transducer unit array is used in its expression.Here, this method for ultrasonic imaging 600 starts from step 602, is designated as " beginning " here.The transducer of 600 pairs of moulding of this method for ultrasonic imaging provides a series of time delayses to send signals, shown in step 604, so that sound wave is shone in the patient body on the desired zone.Time-delay will be calculated based on the focusing geometric arrangement shown in Figure 10 and by any variation of propagating the time-delay distribution that causes in the over cap 206.
According to this improved method for ultrasonic imaging 600, the acoustic energy that is produced is propagated by over cap 206, and this over cap can be designed to the mirror image near shapes such as bidimensional transducer unit arrays 502,552, as shown in step 606.In another embodiment, bidimensional transducer unit array can be essentially plane and have the over cap 206 of stacked non-uniform thickness.
As mentioned above, the shape of bidimensional transducer unit array 502,552 can be selected based on series of factors, and these factors comprise the patient comfort, the Ultrasound Instrument operator is met ergonomics, obtainable patient's sound window and some other factors.
Then in step 608, obtain the ultrasonic echo of reception, and preferably use with the same bidimensional transducer 202 of the execution sending function described in the step 604 and 606 and handle.In case the ultrasonic echo that receives is converted to a voltage waveform by transducer 202, the echo of reception can be delayed time so that image processing system 204 focuses on and shows desired tissue of patient, as shown in step 610.In step 604, calculate this time-delay based on the focusing geometric arrangement shown in Figure 10 and by any variation of propagating the time-delay distribution that causes in the over cap 206.Should be appreciated that method step 604 to 610 can be repeated to carry out to carry out the ultrasonic diagnosis inspection as required.Any number input that Ultrasound Instrument operator produces can be used to finish this method for ultrasonic imaging 600, shown in step 612, is designated as " end " here.
As shown in Figure 7A, transducer 700 comprises a main body 702 and an over cap 706.This over cap 706 comprise basic for sphere shape organize composition surface 712, for example organize the composition surface to constitute the part of spheroid usually.
As shown in Figure 7A, the outside surface of organizing composition surface 712 or over cap 206 by moulding so that patient and Ultrasound Instrument operator all feel comfortably cool.Should be appreciated that and to select special shape according to inspect-type, patient's organize size and/or other factors.The configuration that this embodiment is such can make acoustic energy send and along usually extending or with this acoustic energy of propagated of certain angle extension with the longitudinal axis 716 of transducer 702 is common from transducer 702.Best, organize composition surface 712 with length X 7Contact is to provide the suitable transverse cross-sectional area that cooperates with object 30, so that the acoustic energy of appropriate amount can propagate into object 30 from transducer 702.
Shown in Fig. 7 B, the composite geometric of the modification of embodiment described in its presentation graphs 7A.More specifically, shown in Fig. 7 B, over cap 706 comprises mainly by radius R 1What limit organizes composition surface 712 (in planimetric map).By radius of curvature R 1The surface that limits carries out the transition to by radius of curvature R in its each end 2The face that limits.Best, radius R 2By allowing with the good sound wave coupling of patient and keeping the length of high degree of comfort to determine.Though radius R 2Be expressed as comparing R 1Length only short slightly, but also have some possible relations, these relations comprise the composition surface of organizing of basic sphere shape that the outside surface by over cap 706 shown in Fig. 7 A constitutes.
Fig. 8 A represents the transducer 800 of another embodiment.This transducer 800 has a main body 802 and an over cap 806.Over cap 806 is designed to a kind of over cap 806 of non-focusing sound wave, and it follows the shape of following bidimensional transducer unit array (not shown) basically.Best, over cap 806 has the moulding that is similar to a right cylinder part and organizes composition surface 812.
As shown in Fig. 8 A, transducer 802 can be designed to constitute one and organize composition surface 812, the width X that it has 8Selected the propagation that helps acoustic energy.But, as shown in the figure, also can select the sound window of this width to use one suitably to select.More specifically, if over cap 806 will use, then for example can select width X during a breast imaging process 8, so that try hard to improve the rib of transducer adjacent arrangement in treating imaging health 30 such as the location between rib 832 and 834.When locating like this, will help in the middle of rib, propagating efficiently and being deep in the body from the acoustic energy of transducer 802.As shown in Fig. 8 A, it is cylindrical that over cap 806 can be essentially, so that make the acoustic energy sound window by being made of rib 832 and 834 effectively.
As above described for the substantially spherical embodiment of transducer 702 among Fig. 7 B, when from (Fig. 8 B) when the side is seen, the composition surface 812 of organizing that is formed on over cap 806 outside surfaces can be by radius of curvature R 3Limit.The transition of this every end in tissue composition surface can be by radius of curvature R 4Limit, the latter is relative radius R on length 3Change to some extent.The situation of over cap 806 expressions shown in Fig. 8 B is R 4Less than R 3Such setting makes to be organized composition surface 812 to have to organize face flat relatively on the engaging zones.Therefore, organize composition surface 812 can be regarded as providing the communication media of approaching the best, because the inlet point of its main favourable land productivity between the rib that limits for how much.
Expection formative tissue composition surface 712 and 812 over cap 706 and 806 outside surface are bent usually and can be convenient to organize aiming at of composition surface and window.More specifically, when organizing the composition surface by suitable sizing, the outside surface of over cap 706,806 is tending towards being bonded on the rib, as on rib 832 and 834, can make thus and organize the composition surface to be embedded between the rib.Therefore, these surface trends make and organize the composition surface to aim at the sound window.These curved surfaces can increase patient's comfortableness during imaging process, because non-flexure plane can cause the uncomfortable of part.
Should be appreciated that over cap 706 (Fig. 7 B) and 806 (Fig. 8 B) only are examples.The embodiment of some improved transducer need be provided with complicated over cap and reach at X, Y, the bidimensional transducer unit array 502,522 that changes on the Z coordinate direction (seeing Fig. 5 A, 5B and 10).All these change all among considering and in the scope of this improved ultrasonic transducer.
Operation
As shown in Figure 9, a preferred embodiment of its expression transducer 202 is bonded on the representational sound window with being operated.As an example, this transducer suitably is positioned on the intercostal inlet point of a sound window 902 or a representational chest 904, thus can be to heart 906 ultrasonic imagings.For example by shown in Fig. 9, it is the structure of how much qualifications that the inlet point of intercostal is tending towards, and promptly the intercostal inlet point provides the borderline region that can propagate acoustic energy (acoustic energy can not see through bone, thus will be useful to imaging).Because the shape of over cap 706,806 uses the intercostal inlet point to provide the ability of breastbone interior tissue imaging to greatly increase.In addition, have to the material of the over cap 706,806 of the very similar acoustic impedance of object and be tending towards increasing the acoustic energy total amount of propagating by the intercostal inlet point.As mentioned above, acoustic energy can and receive in two modes in transmission and laterally reach on vertical two dimensions by the electrofocusing, so that suitably make the heart tissue imaging.
Should emphasize that the embodiment of above-mentioned improved ultrasonic transducer, the embodiment of especially any " preferably " only reach as possible embodiment and only be used to illustrate to be expressly understood the principle of transducer.Do not depart from substantially that the embodiment to above-mentioned improved ultrasonic transducer can make many variations and modification under the situation of spirit of the present invention and principle.
For example, be used for medical application, the ultrasonic imaging system 204 as being used for patient though transducer described herein 202 relates to, this system also can be used for various other application.In addition, the various surfaces relevant with over cap 206 have been described here, so that can be with transducer 202 sound window location relatively easily.In other embodiments, one or more these faces can form the part of transducer main body, as on the transducer front end, so that similar functions to be provided.Here all these variations and modification is intended to be included in the disclosure and the scope of the present invention and protects by appended claims.

Claims (22)

1. acoustic imaging system, it comprises:
The transducer that comprises bidimensional transducer unit matrix array, this transducer has and is configured to the over cap that cooperates with the transducer main body, this over cap is stacked in above the bidimensional transducer unit matrix array, and the protected lid of the acoustic energy of over cap mechanically guides and wherein protected lid of transducer unit matrix array and the encirclement of transducer main body so that incide; And
Image processing system; it is connected with transducer and is designed for providing a plurality of mutual incoordinate pumping signals to a plurality of transducer units in time; send acoustic energy so that bidimensional transducer unit matrix array produces acoustic energy in time and passes over cap, make the acoustic energy that passes the over cap transmission thus by electron focusing.
2. according to the acoustic imaging system of claim 1, wherein over cap comprises acoustical material, and the acoustic impedance that this acoustical material has is corresponding to the acoustic impedance of the object for the treatment of imaging.
3. according to the acoustic imaging system of claim 1, wherein the one dimension at least in the bidimensional transducer unit matrix array is crooked.
4. according to the acoustic imaging system of claim 1, wherein over cap is configured to have different-thickness.
5. according to the acoustic imaging system of claim 1, wherein the acoustic impedance that has of over cap is between about 1.3Mrayl and 1.7Mrayl.
6. according to the acoustic imaging system of claim 1, wherein over cap has band and organizes the transducer mating part on composition surface, this transducer cooperative end part to be designed to engage with the transducer main body, and this tissue composition surface constitutes the part of primary circle cylinder.
7. according to the acoustic imaging system of claim 6, wherein this tissue composition surface constitutes the part of basic sphere.
8. according to the acoustic imaging system of claim 1, wherein the transducer main body hand that is suitable for the person of being operated on ergonomics is caught.
9. according to the acoustic imaging system of claim 1, wherein this over cap has a kind of shape, and this shape can reduce the Ultrasound Instrument operator and produce the possibility that repeats to move injury.
10. according to the acoustic imaging system of claim 1, wherein the non-homogeneous sound wave time-delay that caused by over cap by compensation of this image processing system acoustic energy electron focusing that will send is on a target.
11. according to the acoustic imaging system of claim 10, wherein electronic compensation is the function of impact point position.
12. acoustic imaging system according to claim 1; wherein this image processing system receives a plurality of mutual incoordinate receiving mode signal from a plurality of transducer units, and the incident acoustic energy on a plurality of transducer units of bidimensional transducer unit matrix array of over cap is passed in these receiving mode signals representatives.
13. according to the acoustic imaging system of claim 12, wherein this image processing system electron focusing is by the acoustic energy of this over cap reception.
14. according to the acoustic imaging system of claim 13, wherein electron focusing comprises the compensation to the non-homogeneous sound wave time-delay that is caused by over cap.
15. according to the acoustic imaging system of claim 13, wherein electronic compensation is the function of impact point position.
16. the acoustic imaging system according to claim 15 also comprises: the device that is used to enter the sound window for the treatment of the imaging object.
17. according to the acoustic imaging system of claim 16, wherein this access to plant comprises transducer is placed between the rib of adjacent arrangement of a patient body.
18. be used for the method to patient's acoustics imaging, it may further comprise the steps:
Setting has the transducer of bidimensional transducer unit matrix array, this transducer has and is configured to the over cap that cooperates with the transducer main body, this over cap is stacked in above the bidimensional transducer unit matrix array so that the protected lid of acoustic energy that sends and enter object from over cap mechanically guides and wherein bidimensional transducer unit matrix array and over cap by moulding to reduce the uncomfortable of patient;
Produce a plurality of time-delays and send each transducer unit that signal is separately controlled bidimensional transducer unit matrix array, so that to passing the transmission sound wave electron focusing of over cap; And
On each transducer unit of separately controlling of bidimensional transducer unit matrix array, receive the echo of a plurality of time-delays responses, and to passing the reception sound echo electron focusing of over cap.
19., also comprise the reflected sound Echo Processing to produce the step of image according to the method for claim 18.
20., further comprising the steps of according to the method for claim 18:
Sound window near patient; And
Send acoustic energy and acoustic energy is entered in the patient body by over cap by the sound window.
21. according to the method for claim 18, the step that wherein produces and receive also comprises:
In the vertical direction electron focusing acoustic energy; And
Electron focusing acoustic energy in a lateral direction.
22., wherein be included in formation sound window between patient's the rib of adjacent arrangement near the step of sound window according to the method for claim 20.
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DE60222476D1 (en) 2007-10-25

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